Apparatus for the aerosolization of large volumes of dry powder

ABSTRACT

The claimed subject matter relates to a device for dosing and aerosolization of aerosolizable material. The device comprises: a body with an aerosolization channel with a distal attachment portion connectable to a source of carrier gas which provides pressure pulses to the aerosolization channel; a proximal attachment portion for outputting aerosolized material and a reservoir for receiving aerosolizable material. The reservoir comprises walls and is connected in a gas-tight manner to the body and in fluid connection with the aerosolization channel. At least part of the walls of the device are self-exciting membranes that can be put into oscillation by the pressure pulses.

This is a National Phase Application filed under 35 U.S.C. §371 as anational stage of PCT/EP2010/055345, filed on Apr. 22, 2010, anapplication claiming the benefit under 35 U.S.C. §119 of European PatentApplication No. 09158625.5, filed on Apr. 23, 2009, the content of eachof which is hereby incorporated by reference in their entirety.

The invention relates to a device for dosing and aerosolization ofaerosolizable material, in particular powdery medical substances suchas, e.g., pharmaceutical preparations for inhalation. The device isparticularly suited for the aerosolization of powdery lung surfactantpreparations.

BACKGROUND OF THE INVENTION

Devices for aerosolization (“dry nebulization”) of aerosolizable(“nebulizable”) dry material are known to the skilled person. Forexample, for the aerosolization of powdery pharmaceutical preparations,so-called dry powder inhalers (DPIs) have been described. In thesedevices, an aerosolizable material, for example a powdery medicalsubstance, is acted upon by a compressed gas or carrier gas in aspecially provided chamber and, within this chamber, is converted to astate which is referred to as aerosol or dry mist. The particles of thematerial are in this case present in a preferably uniform and finelydispersed form across the entire volume of compressed gas or carrier gasand are then discharged from the chamber in this state via suitabledevices.

Such devices can be used for administration of medical substances tospontaneously breathing or ventilated patients. For use in spontaneouslybreathing patients, the devices are generally connected to a suitablemouthpiece or a breathing mask. In invasive use, i.e. on ventilatedpatients, these devices feed the aerosolized medical substance into aventilator system which then delivers the aerosolized material to thepatient's lung.

In the devices known hitherto for aerosolization of powdery material,however, the problem generally found was that large amounts of medicalsubstances could be delivered to the patient only, if at all, withconsiderable outlay in terms of equipment, for example using extensivemechanical dosing devices. Generally, the known devices were suitablefor the aerosolization of pharmaceutical quantities in the range fromapproximately 1 μg up to approximately 20 mg. However, certain medicalsubstances such as, e.g., lung surfactant preparations, requireadministration of large amounts, for example more than 100 mg or even inthe gram range which, when using conventional DPIs, requires very longinhalation times. A second problem of devices known from the art can bethe reproducibility of the amount of aerosolized material delivered tothe patient. This is particularly the case when during storage or evenduring action of the inhaler the particles of the aerosolizable materialagglomerate to larger particles with a different aerodynamic behaviour.Large particles will have a much smaller chance to reach their target,the deeper lung, since they tend to be deposited in the upper airways orthroat or even somewhere in the inhaling apparatus.

The problem of administering large amounts of aerosolizable materialsuch as lung surfactant preparations in precise doses concerns allsections of the apparatus used for inhalation: the air supply and itscontroller, the aerosolizing unit itself, the piping and valve system(including, where appropriate, the inner surfaces of a ventilatorsystem), and the respiratory endpieces (mask, tube), in other words allsections in which an uncontrolled loss by unwanted deposition ofaerosolized particles and thus reduction of the dose delivered to thepatient and obstruction may occur.

In conventional aerosolizing units, one problem generally found was thatthe aerosolizable material, which is present as a loose charge in astorage container, for example a commercially available pharmaceuticalvial, tends to agglomerate, by reason of its surface quality and/or itsmoisture content, which can result in blockage of a comparatively narrowaperture cross section of the vial. Such agglomeration may also occur inlung surfactant preparations. Such blockages can normally be obviatedonly by suitable mechanical means, in order to ensure a continuousdosing of the aerosolizable material over quite a long period of time.In addition, as already pointed out above, agglomerated particles ofaerosolizable material, for example lung surfactant preparations, arenot generally able to access the lungs with the same efficiency andfollowing the same local distribution/deposition pattern as smaller,non-agglomerated particles.

In the prior art aerosolizing unit of GB 24 848 A, a reservoir ofaerosolizable material is connected via a narrow passage to a chamberinto which supply air is pressed by means of a syringe. Deagglomerationof the aerosolized particles takes place as the supplied air is furtherforced into the reservoir and performs a whirling action therein; whereafter the dispersed aerosolizable material is expelled through thechamber and out of a nozzle towards the patient. In FR 2 598 918 A theaerosolizable material is, in contrast, conveyed by an Archimedean screwinto a jet of compressed air where dispersion takes place.

In many instances it is necessary to ensure rapid and high-doseadministration of aerosolizable material, in a form accessible to thealveoli, into the lungs with a constant dosage, in rapid sequence andover a period of several minutes. Both above-mentioned systems cannot,however, provide administration of high doses of aerosolizable materialand are, due to their geometry and dispersion mechanism, still prone toagglomeration, e.g. in the chamber or in the hopper provided with thescrew, so that accurate dosing remains an issue. In fact, suchadministration was possible, if at all, only with considerable outlay interms of equipment.

WO 2006/108558 A1 discloses a device for dosing and powderaerosolization in which deagglomeration of the aerosolizable material,such as a powdery lung surfactant preparation, is achieved by means ofpressure compensation between the pressure pulses sent into theaerosolization channel of the device. The shear force necessary fordeagglomeration is created by taking advantage of the high pressureduring the pulses. While this system delivers superior results over theknown prior art systems in terms of concentration of aerosolizedmaterial delivered, issues of concern remain regarding residues ofaerosolizable material adhering to the inner surfaces of the system suchas the reservoir walls or the bottom of the aerosolization channel.

A further issue concerns the output characteristics of a dosing devicesuch as the one disclosed in WO 2006/108558 A1. As the dosing deviceuses pressure pulses to deagglomerate, the question arises about theeffect these may have on the patient. The pressure pulses are ofsubstantial magnitude and, thus, the dosing device cannot be connecteddirectly to the patient's breathing front ends such as masks in the caseof spontaneously breathing patients. For ventilated patients, the outputof the dosing device must be connected to the ventilator in order toallow for both adequate and precise dosage, and for the necessary oxygensupply. In the case of infants, moreover, the volume and dosage of thesupplied aerosol as well as the partial pressure of oxygen as well asthe airway pressure are even more critical than in adults and needspecial consideration. Since for infants the conventional approach ofsupplying airborne drugs via pressure respirators and tubes is extremelystressful, specialized equipment and rooms are required.

SUMMARY OF THE INVENTION

It is therefore an object of the present invention to provide a devicefor dosing and aerosolization of aerosolizable dry material whichovercomes the above problems of residues of aerosolizable material andallows essentially all the aerosolizable material present in the deviceto be aerosolized and delivered to the patient, thereby allowing for ayet unachieved dosing accuracy also in the case in which large volumesof dry powder need to be administered.

Since the utility of the device according to the invention is notlimited to the dosing and aerosolization of substances used in a medicalcontext, such as substances used for diagnostics and/or for treatment,it is a further object of the invention to provide a device for dosingand aerosolization of aerosolizable dry material which overcomes theabove problems of residues of aerosolizable material and allowsessentially all the aerosolizable material present in the device to beaerosolized.

It is also an object of the invention to provide a system for dosing andaerosolization of aerosolizable dry material which allows treatment ofspontaneously breathing as well as ventilated patients and can be usedboth with adults and infants.

These objects are achieved by means of a device for dosing andaerosolization of aerosolizable dry material according to claim 1.Further optional and preferred embodiments are defined in the respectivedependent claims.

In a first aspect of the invention, the novel device for dosing andaerosolization of aerosolizable dry material comprises a body with anaerosolization channel having a distal attachment portion connectable toa source of pulsed carrier gas which provides pressure pulses of the gasto the aerosolization channel and a proximal attachment portion foroutputting aerosolized material (the “aerosol”) towards a patient, and areservoir for receiving aerosolized material (“proximal” and “distal” asseen from the patient). It is further preferred that the device has anattachment portion connectable to a source of non-pulsed carrier gasserving to transport the generated aerosol from the aerosolizationchannel or from the reservoir towards the patient. The reservoircomprises walls and is connected in a gas-tight manner to the body andis in flow connection with the aerosolization channel. At least parts ofthe walls are membranes that can be put into oscillation. While thelatter could be realized by any sort of actuator, it is preferred thatthe membranes are self-exciting membranes that can be put intooscillation by the pressure pulses.

Preferably, the novel device comprises means for transferringoscillation energy between different areas of the membranes.Advantageously said means can recircle oscillation energy induced by thepressure pulses. It is preferred to transfer the oscillation energy fromstronger oscillating areas of the membranes to weaker oscillating areas.This serves to compensate for pressure differences between themembranes. Thus activating weaker oscillating areas. Such a transfer canbe assured for example by a tubing connecting the proximal attachmentportion and/or the aerosolization channel and the distal reservoir ofthe device.

The term “membrane” as used herein refers to any sheet-like structurethat is impermeable to gas, liquid and the aerosolizable material, andthat forms at least part of the containment for the aerosolizablematerial in the reservoir. “Self-exciting” as used herein refers to theproperty of the membrane to elastically deform and oscillate in responseto pressure pulses of the carrier gas supplied to the device. As such itis to be understood that, as a function of the membrane's material, themembrane needs to be thin and flexible enough in order to be deformed bythe pressure pulses. Examples of membrane materials are elastic polymerssuch as silicone, but other materials will be apparent to the skilledperson.

By being provided with membrane walls, the inventive device is capableof utilising essentially the complete amount of aerosolizable drymaterial stored in the reservoir and transform it into an aerosolbecause the oscillation of the membrane walls of the reservoir loosensup aerosolizable material, so it can fall into the dosing chamberbeneath the reservoir. The process of aerosolization is, for example,described in WO 2006/108558.

According to the invention it is thus possible to have a uniformly loosecharge of aerosolizable dry material available in the device for dosingand aerosolization after each pressure pulse, as a result of which agradually increasing compaction of the material is avoided and a uniformdosing is guaranteed over a considerable time period. The deviceaccording to the invention thus easily allows aerosolizable material tobe dosed in large amounts in a highly reproducible manner and preferablywithout moving parts. In addition, during the pressure compensationbetween aerosolization channel and reservoir, a loosening of the chargeof the aerosolizable material is achieved. It is thus possiblethat themixture of compressed carrier gas and material predominantly containsdeagglomerated particles, preferably exclusively or almost exclusivelyparticles having the size of the primary, non-agglomerated particles ofthe aerosolizable material. If the aerosolizable material is in the formof a powdery medical substance such as, e.g., powdery lung surfactant,it is possible that the primary particles of the medical substancelocated in the reservoir are present in the mixture of compressed gasand material. To this extent, the device according to the inventionpermits, preferably completely free of mechanical moving parts, optimalaerosolization of the aerosolizable dry material even down to the sizeof the primary particles.

In the preferred case that the device is used for dosing andaerosolization of substances for therapeutic and/or diagnostic purposes,the size of the primary particles of the aerosolizable materialpreferably corresponds to a mass median aerodynamic diameter (MMAD)which is such that the particles are able to access the lungs, i.e. thesite of action in the airways or the alveoli of the lungs. The MMAD ofparticles that can access the lungs is in the range of 1 to 5 μm. Thedesired MMAD range, according to the invention, of the particles in themixture of compressed gas and material is consequently 1 to 5 μm.

Preferably, a funnel portion tapered towards the aerosolization channelis provided in the body between the reservoir and the channel, and thewalls of the funnel portion are self-exciting membranes. The funnelportion is where the aerosolizable material falls to and accumulatesfrom the reservoir before entering the aerosolization channel. Thedifferential pressure pulses generated as a result of the pressurepulses utilizing the Venturi principle create a pressure gradient whichserves to suck the aerosolizable material into the aerosolizationchannel and entrains it into the carrier gas stream, by this generatinga highly concentrated aerosol. As the walls of the funnel portion areself-exciting membranes, no material accumulated in the funnel portionwill be left adhering to its walls and substantially all of it can beentrained in the carrier gas.

The reservoir may preferably be provided with a lid that comprises amembrane towards the reservoir. While the cover as such allows thereservoir to be (re)filled, the membrane on the cover will alsooscillate and support a complete deagglomeration and detachment ofaerosolizable material from the inner surfaces of the reservoir. Ifdesired, between membrane and lid a gas- and/or humidity absorber can beinserted.

Additionally, a self-exciting membrane may be provided as part of thebottom of the aerosolization channel beneath the connection thereof withthe reservoir. When aerosolizable material falls into the aerosolizationchannel, not all of it is always immediately entrained in the carriergas stream, and some material may deposit and accumulate beneath thementioned connection. By providing this area with a self-excitingmembrane, the pressure pulses sent through the aerosolization channelexcite this membrane to oscillate so that the material is reentrained inthe carrier gas. This configuration can be termed a “passivelycontrolled” membrane. It is also conceivable to dispose an actuatorconnected to the membrane so as to drive the membrane to oscillate. Thisis called “actively controlled”.

Finally, it is preferred that the reservoir and the body are integrallyformed. This has the advantage that a disposable device can be providedin which the total dose of aerosolizable material is carefullycontrolled by the manufacturer and contamination and wrong dosage due tofilling inaccuracies can be prevented.

In a second aspect of the invention, a system for dosing andaerosolizaticn of aerosolizable dry material comprises theabove-described device for dosing and aerosolization of aerosolizabledry material. In addition, a first hollow spacer is connected to theproximal attachment portion of the device and comprises a distal portionhaving inner walls tapered towards the proximal attachment portion, anda proximal portion having inner walls tapered towards the patient, withpreferably a central cylindrical portion there between.

The term “spacer” as used herein refers to an additional piece ofpathway for respiratory or carrier gas/aerosol to traverse, whichintroduces expansion space for the pulsed gas stream. The geometry ofthe first hollow spacer allows to dampen the pressure pulse of the gascarrying the aerosol to the patient and to reduce at the same time theassociated noise, much in the same way as a silencer. Thus, both forspontaneously breathing and for ventilated patients, the aerosol arrivesmore uniformly and without unacceptable pressure spikes.

According to a preferred embodiment, the inner walls of the distalportion, the central portion and/or the proximal portion of the firsthollow spacer comprise self-exciting membranes. When a differentialpressure pulse arrives in the system, the membranes oscillate due totheir elasticity so that this construction avoids that particles fromthe aerosol adhere to and stay on the walls of the spacer.

It is also preferred that an annular gap is provided between the distaland the central portions of the first hollow spacer, which isconnectable to an auxiliary air supply. This annular gap can be suppliedwith auxiliary air that rinses the inside of the spacer and makes sureno residue of aerosolizable material stays adhered to the wall. It ismost preferred that the geometry of the annular gap allows formation ofa sheath flow of auxiliary air along the walls of the cylindrical partof the spacer, thus ensheathing the aerosol stream entering the spacerand efficiently helping to avoid the aerosolized particles to deposit onthe spacer's walls.

In a preferred embodiment, the system according to the second aspect ofthe invention further comprises a second hollow spacer connected to theproximal portion of the first hollow spacer and distally to a patientconnector, the second hollow spacer having an ambient air inlet with anon-return valve provided at the distal end and an exhaled gas outletprovided at the proximal end of the second hollow spacer. The secondhollow spacer preferably has a larger cross-section and volume than thepreceding first hollow spacer, and may preferably be cylindrical,although the invention does not provide any limitation on shape.

This arrangement is particularly advantageous for administration ofaerosolized material to spontaneously breathing patients. Like the firsthollow spacer, the second hollow spacer serves to attenuate thedifferential pressure pulses coming from the supply of compressed airthrough the dosage and aerosolization device and to reduce theassociated noise. But it also has the function of providing anintermediate storage for the aerosol, that is the aerosolized materialentrained in the carrier gas. From this intermediate storage, which isconnected to the patient's mouth piece, a spontaneously breathingpatient can inhale the predetermined dose of aerosolized material. Dueto the expanded cross-section and larger volume of the second hollowspacer with respect to the first hollow spacer, the negative respiratorypressure necessary to draw and inhale the aerosolized material from thesecond hollow spacer does not become excessive as would be the case ifthe dosage and aerosolization device and first hollow spacer weredirectly connected to the patient. Moreover, inhalation of aerosolizedmaterial from the first or second spacer is further facilitated by theprovision of auxiliary air as described above.

In an alternative preferred embodiment, the aerosolization device isconnected to a ventilator system operated as CPAP System (continuouspositive airway pressure) delivering ventilatory support to a patient.In such a setup, the aerosol is introduced into a ventilator or CPAPsystem via a T-connector to a patient side respiratory front end. Thissystem provides numerous advantages to patients on mechanicalventilation or on ventilatory support, in particular in case of infantsand neonates. In acute situations, these little patients may needcarefully controlled administration of aerosolized medical substances.By connecting the ventilator or CPAP system and the dosing andaerosolization device via a T-connector that is connecting the device inparallel to the respirator, it is possible to control both how much airor oxygen is provided from the ventilator (by controlling the air and/oroxygen pressure) and, separately, how much aerosolized material isprovided to the patient. Furthermore, in contrast to delivery of theaerosol into the inspiration branch of the respirator, thisconfiguration allows for higher aerosol concentrations in the gasdelivered to the patient since dilution is minimized.

As mentioned above means can be provided to transfer oscillation energyfrom one area of the membranes to another.

Preferably, a compensation tubing is provided between the interior ofthe first hollow spacer and the interior of the funnel portion. Thistubing serves to compensate for pressure differences between spacer andreservoir and at the same time to activate the funnel membrane.

The above-described systems may be integrated in standard ventilatorsystems for routine administration/addition of aerosolizable material,such as lung surfactant, to the respiratory gas.

It is obvious to the person skilled in the art that the aerosolizationdevice as described hereinabove can be used in a variety of technicalfields. Actually the device according to the invention will beapplicable whenever efficient and uniform aerosolization of powders isdesired. While preferred uses of the device according to the inventionare in the field of therapy and administration of inhalable drugs,pharmaceutical preparations and other medical substances, in particularlung surfactant, the device will be useful for the aerosolization of anysort of aerosolizable substances in the range of less than 100 mg up toseveral grams of substance. It is even conceivable that an adequatelysized version of the device allows aerosolization of even higher amountsof substances up to technical scales. The particle size or particle sizedistribution of the material to be aerosolized will depend on theparticular application. For example, as is known from the art, particlesto be administered to the lung by inhalation ideally will have a size inthe range of 1-5 μm MMAD. Of course, the device according to theinvention is not limited to aerosolization of particles in this sizerange. Rather, smaller as well as larger particles would lend themselvesfor aerosolization by use of this device. To give an example, powdercoating of workpieces which has gained considerable importance in recentyears would be a possible application where relatively large quantitiesof particles having a very small size (e.g., <1 μm) have to beaerosolized.

Accordingly, the present invention relates to a device for dosing andaerosolization of aerosolizable material comprising a body with anaerosolization channel having a distal attachment portion connectable toa source of carrier gas which provides pressure pulses of the gas to theaerosolization channel and a proximal attachment portion for outputtingaerosolized material towards a patient, a reservoir for receivingaerosolizable material, the reservoir comprising walls and beingconnected in a gas-tight manner to the body and in fluid connection withthe aerosolization channel, characterized in that at least part of thewalls are self-exciting membranes that can be put into oscillation bythe pressure pulses.

The present invention also relates to the above device, wherein a funnelportion tapered towards the aerosolization channel is provided in thebody between the reservoir and the channel, and wherein walls of thefunnel portion are self-exciting membranes.

The present invention also relates to any of the above devices, whereinthe reservoir is provided with a top cover and the top cover comprises aself-exciting membrane towards the reservoir.

The present invention also relates to any of the above devices, whereina self-exciting membrane is provided in a wall of the aerosolizationchannel beneath the connection thereof with the reservoir.

The present invention also relates to any of the above devices, whereinthe reservoir and the body are integrally formed.

The present invention also relates to any of the above devices, whereinthe reservoir is connected with the aerosolization channel via a valve.In one embodiment, the valve is a rotary valve.

In summary the present invention uses the energy of a pressure pulsegenerated for example by expansion of compressed gas to excite elasticelements. As mentioned before, these elements can be membranes,especially self-exciting membranes. By exciting the membranes energy istaken up from the original pressure pulse, thus weakening this pressurepulse. As a result the aerosolizable material is aerosolized in a morecontinous, constant and homogeneous form compared to a rapid outputinitiated by an unweakened pressure pulse. By such an attenuation of thepressure pulse the aerosole produced is comfortable breathable by apatient.

Additionally an agglomeration of the aerosolizable material, especiallyin the reservoir, is prevented.

BRIEF DESCRIPTION OF DRAWINGS

FIG. 1 is a longitudinal sectional view of an embodiment of a system fordosing and aerosolization according to the invention;

FIG. 2 is schematic view of an embodiment of a system for dosing andaerosolization for use with spontaneously breathing adult patients;

FIG. 3 is schematic view of an embodiment of a system for dosing andaerosolization for use with ventilated infants; and

FIG. 4 is schematic view of an embodiment of a system for dosing andaerosolization for use with ventilated adults.

DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS

In FIG. 1, a longitudinal sectional view of a first embodiment of thesystem for dosing and aerosolization is shown. The system 100 comprisesa device 1 for dosing and aerosolization, in which an aerosolizationchannel 3 is arranged inside a body 2. At its distal end (on the rightin FIG. 1), the body 2 comprises a capillary seat 4 into which acapillary tube holder 14 supporting a capillary tube 13 is fitted. Thiscapillary tube holder 14 can in turn be connected via connecting linesand a valve (both not shown) to a supply of pulsed compressed carriergas. At its proximal end (on the left in FIG. 1), the aerosolizationchannel 3 opens into a dispersing nozzle 5 whose cross section increasescontinuously in a direction extending away from the capillary tube 13.

Above the aerosolization channel 3, the device 1 comprises a reservoir 9for the powdery material to be aerosolized. The reservoir 9 comprises anouter wall 10 and an inner portion having a cylindrical wall 11 andconically tapering wall 12. The walls 11 and 12 are self-excitingmembranes made of, e.g., medical grade silicone having a wall thicknessof about 0.5 mm. Between the outer wall 10 and the cylindrical andconical walls 11 and 12, spaces 6 and 7 are respectively formed. At thebottom, the reservoir 9 forms an aperture 19 located above theaerosolization channel 3 that is partially integral part of the dosingchamber 8. Located above this aperture 19 will be a charge of the powderto be aerosolized (not shown) which may be clumped together to such anextent that almost no grain of aerosolizable material enters theaerosolization channel 3. The whole assembly consisting of parts 5, 3,15, 8, 13, and 4 may be turned by 90 degrees around the apparatus'longitudinal axis to prevent powder from falling into the chamber 8,thus closing the reservoir. Accordingly, said assembly together with thebody 2 forms a rotary valve which allows to interrupt supply of thepowder stored in the reservoir 9 to the dosing chamber 8 andaerosolization channel 3.

On top of the reservoir 9, a lid 16 is provided that tightly closes thereservoir. At the bottom side of the lid, towards the interior of thereservoir, a self-exciting membrane 17 is provided that seals the topopening of the reservoir 9. Above the membrane, a humidity (or generallygas) absorber 18 is included in the cover that eliminates residualhumidity or other trace gases in the reservoir which otherwise couldhave adverse effects. Furtheron, a space is formed between the membrane17 and the humidity absorber 18 (not shown).

In the present embodiment, the reservoir 9 and the body 2 with theaerosolization channel 3 are integrally formed, whereby completegas-tightness and sterility is guaranteed. However, it is to beunderstood that they may also be separate elements that are fittedtogether in an gas-tight manner.

The dispersing nozzle 5 opens into a proximal attachment piece 2 a whichis an integral component part of the body 2. Onto the attachment piece 2a, a hollow spacer 20 is fitted in a gas-tight manner. The spacer 20comprises a cylindrical outer wall 21, a distal portion with conicalinner walls 22 tapered distally, a proximal portion with conical innerwalls 24 tapered proximally, and a central portion having cylindricalwalls 23 arranged there between. As with the reservoir, also the walls22, 23, 24 of the spacer 20 are self-exciting membranes made of, e.g.,silicone. Between the outer wall 21 and walls 22, 23, 24 correspondingspaces 25, 26, 27 are provided. An annular gap is formed between thedistal and central portions of the spacer 20 and is connected to anauxiliary gas supply (not shown).

In operation, pressure pulses of carrier gas enter the aerosolizationchannel 3 of device 1 through the capillary 13 and, due to the pressuredifference created between the gas exiting from capillary 13 and thereservoir 9 by Venturi's principle, aerosolizable material is suckedfrom the reservoir 9 into the aerosolization channel 3, dispersed andentrained in the carrier gas. At the same time, this differentialpressure pulse also acts on the membrane walls 11, 12 of the reservoir 9and the membrane walls 22, 23, 24 of the spacer 20, causing them tobulge and oscillate according to the frequency of the pressure pulses.Thus, aerosolizable material adhering to the walls is reentrained intothe bulk material and free to enter the carrier gas stream.

It is to be understood that in alternative embodiments only some of theinner walls of the device are carried out as self-exciting membranes.For example, in an alternative embodiment only the tapered wall 12 is aself-exciting membrane. Obviously, each inner wall of the device whichis not carried out as self-exciting membrane does not require a hollowspace between this inner and the corresponding outer wall. For example,when only the tapered wall 12 is carried out as self-exciting membrane,spaces 6 and 25-27 are dispensable.

The amount of aerosolizable material that can be administered with thedevices and systems of the present invention exceeds 50 mg and iscoupled with a high precision of dosage. On one hand, the precisionallows the use of drugs having a very narrow “therapeutic window” and onthe other hand the large volumes make the system suitable for use withsubstances that need to be administered in large quantities. Forexample, aerosolizable medical substances other than lung surfactantwhich can be administered by use of the device according to theinvention include antibiotics, nucleic acids, retard formulas,peptides/proteins, vaccines, antibodies, insulin, osmotically activesubstances like mannitol, hydroxyethyl starch, sodium chloride, sodiumbicarbonate and other salts, enzymes (e.g., DNAse), N-acetyl cystein,etc.

Turning now to FIG. 2, an embodiment of a system for dosing andaerosolization 200 is shown, which is employed for large volume drypowder inhalation of spontaneously breathing patients. The system 200comprises the device 1 for dosing and aerosolization and the firstspacer 20 of the first embodiment, wherein additionally a compensationtubing 29 connects the spaces 6, 7 of the reservoir with spaces 25, 26,27 of the spacer 20. On the upstream side, the system 200 comprises acontroller 50 that is connected via a compressed air line 51 to acompressed air supply 52 (e.g., the compressed air supply of a hospital)providing the compressed air through a main connecting line 41 to thedosing and aerosolization device 1. The main connecting line 41 isconnected to the capillary holder 14 (distal attachment portion) of thedevice 1. The flow of the compressed air to the device is regulated by afast-switching solenoid valve 40 which is caused to open and close by acurrent pulse 43 sent from the controller so as to achieve a determinednumber, duration and frequency of air pressure pulses. In use, the flowof compressed air may be triggered automatically by the controller, butmay also be triggered by the breathing of the patient so as to adapt thetiming of aerosolization and the volume of aerosolized material providedin the second spacer to the patient's breathing characteristics.

An auxiliary connecting line 42 supplies un-pulsed air to the annulargap 28 of the spacer 20 (the connection is not shown) to thereby flushthe spacer of residues of aerosolizable material. Both connecting lines41 and 42 comprise filters F to block contamination by undesiredparticles.

On the downstream side, a second spacer 30 is connected to the firstspacer 20. At the same time, an ambient air inlet 31 provided with ano-return valve 32 is provided at the distal end of the second spacer30. At the proximal end of the second spacer 30, a straight connector 34with a mouth piece 35 is positioned, while an exhaled gas outlet 36(optionally with a filter F) branches perpendicularly off the straightconnector 34.

FIG. 3 shows an embodiment of the system for dosing and aerosolizationthat is particularly suited for acute respiratory therapy of very youngchildren such as infants and neonates. Several components which are thesame or are equivalent to those described with respect to FIGS. 1 and 2bear the same reference numerals and will not be discussed again. Thesystem 300 comprises the device 1 for dosing and aerosolization and thespacer 20, and a controller 50 which is connected to it in the same wayas in the embodiment of FIG. 2. Connected to the output of spacer 20 isa ventilator tubing 60 that in turn connects to the first port of aT-piece 61. Further, in this embodiment a ventilator in CPAP mode 70 isprovided that supplies respiratory gas via respiratory gas line 64 to amanifold 65 while keeping the ventilator pressure at a constant level.From the manifold 65, a common ventilating line 62 connects to thesecond port of the T-piece 61. The third port is connected to anasopharyngeal tube 66 that is introduced through the infant's nose sothat its tip is positioned just above the glottis.

Further, a flow rate sensor 67 is disposed at the manifold to measurethe gas flow rate V3 of the gas in common line 62. The measurementsignals are fed back to the ventilator 70, which directly controls thepressure in line 64 and in line 63 by controlling the respective flowrates, and therefore indirectly controls V₃. By means of this pressurecontrol additional flow from the disperser dosing unit causes V₃ to bedown regulated so that the pressure and hence total flow to the infant(V5) is kept constant.

In addition, an oxygen sensor 69 is provided at the third port of theT-connector 61, monitoring oxygen content of the respiratory gas mixtureactually administered to the lungs of the infant. The respectivemeasurement signals are fed back to the ventilator 70, where togetherwith the flow rate information a comprehensive picture of the propertiesof the supplied respiratory gas mixture is obtained. These propertiesare then in turn controlled by the ventilator 70. In summary, byconnecting the device 1 in parallel with the respiratory system, itbecomes possible both to provide oxygen-rich respiratory gas and thecorrect dose of aerosolized material, such as lung surfactant.

Finally, turning to FIG. 4, another embodiment of a system for dosageand aerosolization is shown. The system 400 is used with ventilatedadult patients and comprises the device 1 for dosing and aerosolization,the controller 50, a ventilator 71 and a hollow spacer 80. Thecontroller is connected in the above-described manner to a hospital airsupply 52 and via a main connecting line 41 with valve 40 to the device1, just as described in the foregoing embodiments. However, in thisembodiment, the spacer 80 is much larger than spacer 20, both indiameter and in volume, in order to accommodate the needs of an adultventilated patient. The spacer 80 is connected at its distal end to theproximal attachment piece 2 a of the device 1 and has at its proximalend a straight connector 84 leading to a breathing mask 85. Arespiratory gas inlet 81 with a non-return valve 82 is disposedlaterally on the distal end of the spacer 80 and is connected in theusual manner via a filter and respiratory gas line 64 to the ventilator71. Similarly, at the proximal side an exhaled gas outlet 86 isconnected via a non-return valve 82 and exhaled gas return line 63 tothe ventilator.

The amount of aerosolizable material that can be administered with thedevices and systems of the present invention exceeds 50 mg and iscoupled with a high precision of dosage. On the one hand, the precisionallows the use of drugs having a particularly narrow “therapeuticwindow” and on the other hand the large volumes make the system suitablefor use with substances that need to be administered in largequantities. For example, aerosolizable medical substances other thanlung surfactant which can be administered by use of the device accordingto the invention include contrast agents, antibiotics, nucleic acids,retard formulas, peptides/proteins, vaccines, antibodies, insulin,osmotically active substances like mannitol, hydroxyethyl starch, sodiumchloride, sodium bicarbonate and other salts, enzymes (e.g. DNAse),N-acetyl cystein, etc.

The invention claimed is:
 1. A system for dosing and aerosolization ofaerosolizable material, the system comprising: a body with anaerosolization channel having a distal attachment portion connectable toa source of carrier gas which provides pressure pulses of the gas to theaerosolization channel and a proximal attachment portion for outputtingaerosolized material towards a patient; a reservoir for receivingaerosolizable material, the reservoir comprising at least one wall andbeing connected in a gas-tight manner to the body and in fluidconnection with the aerosolization channel; a funnel portion taperedtowards the aerosolization channel provided in the body between thereservoir and the aerosolization channel; an additional piece of pathwayfor aerosol to traverse configured to introduce expansion space for thepulsed gas stream and thus allow the pressure pulse of the gas arrangedto carry the aerosol to the patient to dampen, the additional piece ofpathway being a first hollow spacer comprising a distal portion havingat least one inner wall tapered towards the proximal attachment portion,and a proximal portion having at least one inner wall and configured totaper towards the patient, with a central cylindrical portiontherebetween haying at least one inner wall, and the additional piece ofpathway further being connected to the proximal attachment portion; anda compensation tubing provided between an interior of the first hollowspacer and an interior of the funnel portion, wherein at least one wallof the funnel portion and the at least one inner wall of the distalportion, of the central portion and/or the proximal portion of the firsthollow spacer comprise self-exciting membranes that can be put intooscillation by the pressure pulses, and wherein corresponding spaces areprovided between such self-exciting membranes and an outer wall.
 2. Thesystem of claim 1, wherein the reservoir is provided with a top coverand the top cover comprises a self-exciting membrane towards thereservoir.
 3. The system of claim 1, wherein a self-exciting membrane isprovided in a wall of the aerosolization channel beneath the connectionthereof with the reservoir.
 4. The system of claim 1, wherein thereservoir and the body are integrally formed.
 5. The system of claim 1,wherein the reservoir is connected with the aerosolization channel via avalve.
 6. The system of claim 5, wherein the valve is a rotary valve. 7.The system of claim 1, wherein an annular gap is provided between thedistal and the central portions of the first hollow spacer, which isconnectable to an auxiliary air supply.
 8. The system of claim 7,further comprising a second hollow spacer connected proximally to theproximal portion of the first hollow spacer and distally to a mouthpiece, the second hollow spacer having an ambient air inlet with anon-return valve provided at the distal end and an exhaled gas outletprovided at the proximal end of the second hollow spacer.
 9. The systemof claim 1, further comprising a ventilator or a CPAP valve, wherein theproximal portion of the first hollow spacer and the ventilator or CPAPvalve are connected via a Y-connector to a patient side respiratoryfront end.
 10. The system of claim 9, wherein an air delivery port ofthe ventilator and an exhaled gas port of the ventilator are connectedto the Y-connector via a manifold.
 11. The system of claim 10, wherein aflow sensor is provided at the manifold, and an oxygen sensor isprovided at a patient side port of the Y-connector.
 12. The system ofclaim 9, wherein the patient side respiratory front end is anasopharyngeal tube.
 13. The system of claim 9, wherein the first hollowspacer is connected proximally to a respiratory front end, wherein thefirst hollow spacer is further connected at its distal end via anon-return valve to an air delivery port of the ventilator, and isfurther connected at its proximal end to an exhaled gas port of theventilator.
 14. The system of claim 9, wherein any one of a flow sensorand an oxygen sensor is provided between the ventilator or CPAP valveand the patient side respiratory front end.
 15. The system of claim 1,wherein the system further comprises: a control box for providingpressure pulses of carrier gas to the aerosolization channel, thecontrol box being connectable to a hospital compressed air supply andconnected to the distal attachment portion of the body via a valve,wherein the control box is adapted to control the number and frequencyof the carrier gas pressure pulses and the flow rate of the carrier gasby controlling the valve.